**Biosensors for Aflatoxins Detection**

#### Lucia Mosiello and Ilaria Lamberti

*ENEA, Italian National Agency for New Technologies, Energy and the Environment, Rome, Italy* 

#### **1. Introduction**

146 Aflatoxins – Detection, Measurement and Control

Van Egmond, H. P., Paulsch, W. E., & Schuller, P. L. (1978). Confirmatory test for aflatoxin

Whitaker, T. B., Dickens, J. W., & Manroe, R. J. (1976). Variability associated with testing

cottonseed for aflatoxin. *Journal of American Oil and Chemical Society,* Vol.53, pp.

M1 on thin layer plate. *Journal of AOAC,* Vol.61, No.4, pp. 809-812

502-505

The availability of rapid and reliable methods for rapid determination of small molecules, as contaminants in food samples, including Aflatoxins, is an increasing need also for human health. In order to monitoring food contaminants, as Mycotoxins (MTXs) Gas Chromatographic (GC) and High Pressure Liquid Chromatography (HPLC) methods are generally utilized, due to their high detection sensibility and selectivity. However, GC and HPLC analyses are time consuming and needs sample pre-treatment or pre-concentration procedures. Immunoassays and biosensors are becoming a recognized alternative or complementary to conventional analytical techniques for the detection of mycotoxins, as Aflatoxins.

Recently, biosensors based on the use of monoclonal or polyclonal antibodies have seen a great development in the field of small molecules analytical determination and specifically in the mycotoxins analyses. Among biosensors for mycotoxins monitoring, optical or electrochemical devices for Aflatoxins detection were described by different authors. The present Chapter describes the different biosensors for Aflatoxins developed and utilized in food analysis. The absence of cross-reactivity obtained with most of these biosensor, the possibility of on-line measurement, the absence of sample pre-treatment, can really put it in competition with other conventional systems such as HPLC and ELISA.

Chapter describes also main biosensors features and vantages for these innovative devices and various examples of biosensors and reviews some biosensors for Aflatoxins and other mycotoxins detection methods, as microarray.

In particular, we will focus our attention on biosensors developed for mycotoxins detection that utilize immunoglobulins or aptamer showing affinity for a correspondent analyte, associated to various transduction elements. Various biosensing platforms will be introduced, including, but not limited to, surface plasmon resonance and quartz microbalance crystals. Examples of biosensors array, as microarray, detecting Aflatoxin and Fumonisin will be also presented. Some of these biosensing devices were developed in our laboratories and the sensing performance of each device will be evaluated and compared in terms of sensitivity and detection limit.

Analytical methods used for mycotoxins determination are mainly based on TLC, HPLC or ELISA. Actually biosensor and microsystem technologies are used for different applications including studies of human and veterinary diseases, drug discovery, genetic screening, clinical and food diagnostics. According to these approaches the aim of many authors was to transfer the methods of the immunological assay from microtiter plates into a biosensor format in order to develop a rapid, sensitive and inexpensive method for the detection of

Biosensors for Aflatoxins Detection 149

A biosensor is an analytical device for the detection of an analyte that combines a biological component with a physicochemical detector component. The most commune biosensor

 the *sensitive biological element,* or biological material (e.g. tissue, microorganisms, organelles, cell receptors, enzymes, antibodies, nucleic acids, etc.), a biologically derived

 the *transducer* or the *detector element* (works in a physicochemical way; optical, piezoelectric, electrochemical, etc.) that transforms the signal resulting from the interaction of the analyte with the biological element into another signal (i.e.,

associated electronics or signal processors that are primarily responsible for the display

Main advantages of biosensors technology in comparison with traditional analytical methods are fast detection (minutes) and response (seconds), high sensitivity (typically nM, improved sensitivity with nanoparticles pM and better), their high selectivity, easy preparation and operation assay method. In addition most of these devices are reusable and

The methodology of surface chemistry is the basic knowhow for obtaining reproducible

The key points to consider when selecting an appropriate surface and coating procedure are a low degree of unspecific binding sites and uniform distribution of functional groups on

results with biosensors and various strategies can be used (Gagliardi et al, 2007).

material. The sensitive elements can be created by biological engineering.

transducers) that can be more easily measured and quantified;

scheme is reported in Fig.2 and it is consists of 3 parts:

of the results in a user-friendly way.

Fig. 2. Scheme of a Biosensor

the substrate surface.

show low cost assay (Typically less then 10 EUR/sensor).

**3. Biosensors** 

mycotoxins for food safety applications. Microarray and biosensor technology enables the fast and parallel analysis of a multitude of biologically relevant parameters. Not only nucleic acid-based tests, but also peptide, enzyme and antibody assays using different formats of biosensor evolved within the last decade. Antibody-based microarrays are a powerful assay technology that can be used to generate rapid detection of analytes in complex samples which, in our opinion, is also potentially useful for the generation of rapid immunological assay of food contaminants.

### **2. Aflatoxins**

Mycotoxins are secondary metabolites that moulds produce naturally. Due to their ubiquitous presence in foodstuffs and their potential risk for human health, prompt detection is important. It is estimated that approximately 25% of the world's crops are contaminated to some extent with mycotoxins. Some mycotoxins (e.g.,aflatoxins) have been designated biowarfare agents due to their potential carcinogenicity. (Prieto-Simón et al., 2007 ) .

Aflatoxins are highly toxic and carcinogenic secondary metabolites produced mainly by three anamorphic species of the genus *Aspergillus*: *A. flavus*, *A. parasiticus* and *A. nomius*  (Ehrlich et al., 2003). They are the most potent, naturally-occurring carcinogens known and have been linked to liver cancer and several other maladies in animals and humans (Turner *et al.*, 2003; Valdivia et al., 2001; Otim et al., 2005).

When aflatoxin B1 (AFB1), the most toxic aflatoxin, is ingested by cows through contaminated feed, it is transformed into aflatoxin M1 (AFM1) through enzymatic hydroxylation of AFB1 at the 9a-position (see below) and has an approximate overall conversion rate equal to 0.3 to 6.2%.

AFM1 is secreted in milk by the mammary gland of dairy cows. Even though it is less toxic than its parent compound, AFM1 has hepatotoxic and carcinogenic effects. This toxin, initially classified as a Group 2B agent, has now been reclassified as Group 1 by the International Agency for the Research on Cancer (IARC).

Another important class of MTX are those produced by *Fusarium moniliforme,* a prevalent fungus that infects corn and other cereal grains.

Fumonisin B1 (FB1) is the most common mycotoxin produced by *F. moniliforme*, suggesting it has toxicologic significance. Ingestion of moldy corn infected by *F. moniliforme* or closely related fungi is linked to a higher incidence of primary liver cancer (Ueno et al., 1997) and esophageal cancer in regions of South Africa and China.

Fig. 1. Aflatoxins B1 and M1 and *Aspergillus* fungus

### **3. Biosensors**

148 Aflatoxins – Detection, Measurement and Control

mycotoxins for food safety applications. Microarray and biosensor technology enables the fast and parallel analysis of a multitude of biologically relevant parameters. Not only nucleic acid-based tests, but also peptide, enzyme and antibody assays using different formats of biosensor evolved within the last decade. Antibody-based microarrays are a powerful assay technology that can be used to generate rapid detection of analytes in complex samples which, in our opinion, is also potentially useful for the generation of rapid immunological

Mycotoxins are secondary metabolites that moulds produce naturally. Due to their ubiquitous presence in foodstuffs and their potential risk for human health, prompt detection is important. It is estimated that approximately 25% of the world's crops are contaminated to some extent with mycotoxins. Some mycotoxins (e.g.,aflatoxins) have been designated

Aflatoxins are highly toxic and carcinogenic secondary metabolites produced mainly by three anamorphic species of the genus *Aspergillus*: *A. flavus*, *A. parasiticus* and *A. nomius*  (Ehrlich et al., 2003). They are the most potent, naturally-occurring carcinogens known and have been linked to liver cancer and several other maladies in animals and humans (Turner

When aflatoxin B1 (AFB1), the most toxic aflatoxin, is ingested by cows through contaminated feed, it is transformed into aflatoxin M1 (AFM1) through enzymatic hydroxylation of AFB1 at the 9a-position (see below) and has an approximate overall

AFM1 is secreted in milk by the mammary gland of dairy cows. Even though it is less toxic than its parent compound, AFM1 has hepatotoxic and carcinogenic effects. This toxin, initially classified as a Group 2B agent, has now been reclassified as Group 1 by the

Another important class of MTX are those produced by *Fusarium moniliforme,* a prevalent

Fumonisin B1 (FB1) is the most common mycotoxin produced by *F. moniliforme*, suggesting it has toxicologic significance. Ingestion of moldy corn infected by *F. moniliforme* or closely related fungi is linked to a higher incidence of primary liver cancer (Ueno et al., 1997) and

biowarfare agents due to their potential carcinogenicity. (Prieto-Simón et al., 2007 ) .

assay of food contaminants.

*et al.*, 2003; Valdivia et al., 2001; Otim et al., 2005).

International Agency for the Research on Cancer (IARC).

esophageal cancer in regions of South Africa and China.

Fig. 1. Aflatoxins B1 and M1 and *Aspergillus* fungus

fungus that infects corn and other cereal grains.

conversion rate equal to 0.3 to 6.2%.

**2. Aflatoxins** 

A biosensor is an analytical device for the detection of an analyte that combines a biological component with a physicochemical detector component. The most commune biosensor scheme is reported in Fig.2 and it is consists of 3 parts:


Fig. 2. Scheme of a Biosensor

Main advantages of biosensors technology in comparison with traditional analytical methods are fast detection (minutes) and response (seconds), high sensitivity (typically nM, improved sensitivity with nanoparticles pM and better), their high selectivity, easy preparation and operation assay method. In addition most of these devices are reusable and show low cost assay (Typically less then 10 EUR/sensor).

The methodology of surface chemistry is the basic knowhow for obtaining reproducible results with biosensors and various strategies can be used (Gagliardi et al, 2007).

The key points to consider when selecting an appropriate surface and coating procedure are a low degree of unspecific binding sites and uniform distribution of functional groups on the substrate surface.

Biosensors for Aflatoxins Detection 151

solutions of the target analyte the LOD of the assays were 0.3 and 0.2 ng ml-1 for T-2 and AFB1 respectively, while the sensitivity was 1.2 ng ml-1 for both. For Aflatoxin B1, a stability study of electrochemical plate was also performed. Moreover, the matrix effect was

The specificity of the assay was assessed by studying the cross-reactivity of the MAb (Monoclonal Antibody) towards other aflatoxins. The results indicated that the MAb could readily distinguish AFB1 from other toxins, with the exception of AFG1 (Piermarini,

In the field of enzymatic/amperometric biosensor application an electrochemical immunosensor for the detection of ultratrace amounts of aflatoxin M1 (AFM1) in food

This sensor was based on a competitive immunoassay using horseradish peroxidase (HRP) as a tag. Magnetic nanoparticles coated with antibody (anti-AFM1) were used to separate the bound and unbound fractions. The samples containing AFM1 were incubated with a fixed amount of antibody and tracer [AFM1 linked to HRP (conjugate)] until the system reached equilibrium. Competition occurs between the antigen (AFM1) and the conjugate for the antibody. Then, the mixture was deposited on the surface of screen-printed carbon electrodes,

The enzymatic response was measured amperometrically. A standard range (0, 0.005, 0.01, 0.025, 0.05, 0.1, 0.25, 0.3, 0.4 and 0.5 ppb) of AFM1-contaminated milk from the ELISA kit was used to obtain a standard curve for AFM1. To test the detection sensitivity of our sensor, samples of commercial milk were supplemented at 0.01, 0.025, 0.05 or 0.1 ppb with AFM1. Immunosensor for Afla M1 described has a low detection limit (0.01 ppb), which is under

Recently an innovative amperometric biosensor for AflatoxinB1 was described. This biosensor was developed using the enzyme conjugate aflatoxin-oxidase (AFO), embedded in sol-gel, linked to multiwalled carbon nanotubes (MWCNTs)-modified Pt electrode and

The covalent linkage between AFO and MWCNTs retained enzyme activity and responsed to the oxidation of afltoxin B1 (AFB1). Its apparent Michaelis-Menten constant for AFB1 was 7.03 μmol·L−1, showing a good affinity. The sensor exhibited a linear range from 3.2 nmol·L−1 to 721 nmol·L−1 (1 ng/ml to 225 ng/ml) with limits of detection of 1.6 nmol·L−<sup>1</sup> (signal-to-noise ratio = 3), an average response time of 44 s (less than 30 s when AFB1 Conc. is bigger than 45 ng/ml), and a high sensitivity of 0.33 × 102 A mol−1·L cm−2. The active energy was 18.8 kJ mol−1, demonstrating the significant catalyzation of AFO for oxidation of

These results demonstrated that AFO act at the unsaturated carbon bond of bisfuran ring in AFB1, to primarily form an unstable compound: oxygen additive product and hydrogen peroxide. This makes a clear choice to use AFO as a recognition receptor for biosensors to

A promising technology for rapid Afaltoxins detection is the surface plasmon resonance biosensor. The principle of surface plasmon resonance is based on the detection of a change of the refractive index of the medium when an analyte binds to an immobilised partner

and the mediator [5-methylphenazinium methyl sulphate (MPMS)] was added.

the recommended level of AFM1 [0.05 µg L-1 (ppb)], and has good reproducibility.

evaluated using two different extraction treatments from corn.

et al., 2007).

products was developed.

was reported for the first time.

AFB1 in this biosensor.

molecule (antibody).

detect this mycotoxin (Li *et al.*, 2011).

**4. SPR biosensor for aflatoxins** 

For this reason during biosensor development and testing particular attention would be focused on


Among biosensors piezo-electric devices are sensors that integrate a biological element with a physiochemical transducer to produce an electronic signal proportional to an analyte which is then conveyed to a detector.

Mass sensitive piezoelectric transducers are usually based on AT-cut quartz crystal covered by gold electrodes. The external alternating voltage induces oscillation of the quartz. The frequency of this oscillation depends on the transducer thickness (Fig.3).

Fig. 3. (a) Mass piezoelectric trasducer; (b) A biosensor antibody-based

In these biosensors the frequency value of the oscillation of the quartz is proportional to the mass of the crystal following the Sauerbrey law and decreases with increasing of the mass (Equation 1, Sauerbrey equation).

$$
\Delta \mathbf{f} = \text{-2.26x10} \cdot \mathbf{f}\_0 \mathbf{2} (\Delta \mathbf{m}/\mathbf{A}) \tag{1}
$$

Responding to the need to achieve high sensitivity and move to the use of disposable probes, several electrochemical immunosensors have recently been reported in literature for the detection of AFB1 (Aflatoxin B1) in corn and barley and AFM1 (Aflatoxin M1) in milk.

In particular, for AFB1 determination, an indirect competitive electrochemical immunoassay has been developed using disposable screen-printed carbon electrodes.

In an another work was presented a biosensing method for detection of aflatoxin B1 and type-A trichothecenes, based on the use of indirect competitive ELISA format coupled with a 96-well screen-printed microplate.

Electrochemical immunoassays for AFB1, T-2, and HT-2 were performed and the activity of the alkaline phosphatase or horseradish peroxidase labeled enzymes were measured using intermittent pulse amperometry (IPA) as electrochemical technique. Using standard

For this reason during biosensor development and testing particular attention would be

Among biosensors piezo-electric devices are sensors that integrate a biological element with a physiochemical transducer to produce an electronic signal proportional to an analyte

Mass sensitive piezoelectric transducers are usually based on AT-cut quartz crystal covered by gold electrodes. The external alternating voltage induces oscillation of the quartz. The

In these biosensors the frequency value of the oscillation of the quartz is proportional to the mass of the crystal following the Sauerbrey law and decreases with increasing of the mass

Responding to the need to achieve high sensitivity and move to the use of disposable probes, several electrochemical immunosensors have recently been reported in literature for the detection of AFB1 (Aflatoxin B1) in corn and barley and AFM1 (Aflatoxin M1) in milk. In particular, for AFB1 determination, an indirect competitive electrochemical immunoassay

In an another work was presented a biosensing method for detection of aflatoxin B1 and type-A trichothecenes, based on the use of indirect competitive ELISA format coupled with

Electrochemical immunoassays for AFB1, T-2, and HT-2 were performed and the activity of the alkaline phosphatase or horseradish peroxidase labeled enzymes were measured using intermittent pulse amperometry (IPA) as electrochemical technique. Using standard

f= -2.26x10-6 f02(m/A) (1)

Surface (on wich sensing layer will be coated) characterisation

Biological reagent (immunoglobulin, nucleic acid, ecc.) characterisation

frequency of this oscillation depends on the transducer thickness (Fig.3).

focused on

 Uniformity of biological element Standard solution preparation

which is then conveyed to a detector.

Calibration and Standard Curve construction

(a) (b)

(Equation 1, Sauerbrey equation).

a 96-well screen-printed microplate.

Fig. 3. (a) Mass piezoelectric trasducer; (b) A biosensor antibody-based

has been developed using disposable screen-printed carbon electrodes.

solutions of the target analyte the LOD of the assays were 0.3 and 0.2 ng ml-1 for T-2 and AFB1 respectively, while the sensitivity was 1.2 ng ml-1 for both. For Aflatoxin B1, a stability study of electrochemical plate was also performed. Moreover, the matrix effect was evaluated using two different extraction treatments from corn.

The specificity of the assay was assessed by studying the cross-reactivity of the MAb (Monoclonal Antibody) towards other aflatoxins. The results indicated that the MAb could readily distinguish AFB1 from other toxins, with the exception of AFG1 (Piermarini, et al., 2007).

In the field of enzymatic/amperometric biosensor application an electrochemical immunosensor for the detection of ultratrace amounts of aflatoxin M1 (AFM1) in food products was developed.

This sensor was based on a competitive immunoassay using horseradish peroxidase (HRP) as a tag. Magnetic nanoparticles coated with antibody (anti-AFM1) were used to separate the bound and unbound fractions. The samples containing AFM1 were incubated with a fixed amount of antibody and tracer [AFM1 linked to HRP (conjugate)] until the system reached equilibrium. Competition occurs between the antigen (AFM1) and the conjugate for the antibody. Then, the mixture was deposited on the surface of screen-printed carbon electrodes, and the mediator [5-methylphenazinium methyl sulphate (MPMS)] was added.

The enzymatic response was measured amperometrically. A standard range (0, 0.005, 0.01, 0.025, 0.05, 0.1, 0.25, 0.3, 0.4 and 0.5 ppb) of AFM1-contaminated milk from the ELISA kit was used to obtain a standard curve for AFM1. To test the detection sensitivity of our sensor, samples of commercial milk were supplemented at 0.01, 0.025, 0.05 or 0.1 ppb with AFM1.

Immunosensor for Afla M1 described has a low detection limit (0.01 ppb), which is under the recommended level of AFM1 [0.05 µg L-1 (ppb)], and has good reproducibility.

Recently an innovative amperometric biosensor for AflatoxinB1 was described. This biosensor was developed using the enzyme conjugate aflatoxin-oxidase (AFO), embedded in sol-gel, linked to multiwalled carbon nanotubes (MWCNTs)-modified Pt electrode and was reported for the first time.

The covalent linkage between AFO and MWCNTs retained enzyme activity and responsed to the oxidation of afltoxin B1 (AFB1). Its apparent Michaelis-Menten constant for AFB1 was 7.03 μmol·L−1, showing a good affinity. The sensor exhibited a linear range from 3.2 nmol·L−1 to 721 nmol·L−1 (1 ng/ml to 225 ng/ml) with limits of detection of 1.6 nmol·L−<sup>1</sup> (signal-to-noise ratio = 3), an average response time of 44 s (less than 30 s when AFB1 Conc. is bigger than 45 ng/ml), and a high sensitivity of 0.33 × 102 A mol−1·L cm−2. The active energy was 18.8 kJ mol−1, demonstrating the significant catalyzation of AFO for oxidation of AFB1 in this biosensor.

These results demonstrated that AFO act at the unsaturated carbon bond of bisfuran ring in AFB1, to primarily form an unstable compound: oxygen additive product and hydrogen peroxide. This makes a clear choice to use AFO as a recognition receptor for biosensors to detect this mycotoxin (Li *et al.*, 2011).

#### **4. SPR biosensor for aflatoxins**

A promising technology for rapid Afaltoxins detection is the surface plasmon resonance biosensor. The principle of surface plasmon resonance is based on the detection of a change of the refractive index of the medium when an analyte binds to an immobilised partner molecule (antibody).

Biosensors for Aflatoxins Detection 153

deviation of the blank measurements. Aflatoxin-free certified T400A maize sample was used

Calibration Curve: Biosensor-based assay was applied for the determination of AFB1 using spiked maize samples (Figure 3). The analysis of the binding of AFB1 to elastase over the concentration range 1−50 μg/kg reported that the response for the optimized assay was linear in the range between 1.67 and 17.8 μg/kg. The calibration procedure was replicated on three different days. The experimentally measured lower limit of the linear range was 1.67 μg/kg of AFB1, whereas the KD was 0.91 μM (≈250 μg/kg) AFB1. The detection limits reached allow us

Recently some authors presented during a Nanotechology Conference a SPR biosensor for

Because one of the main goal in the development of SPR immunosensors is efficient immobilization of antibodies. Conventional methods, such as self-assembled monolayers (SAMs) of alkanethiols cause antibodies to be random oriented. To improve antibody linker and orientation in their work, the authors constructed a novel fusion protein by genetically

The resulting GBP-ProA protein was directly self-immobilized onto SPR gold chip surfaces via the GBP portion, followed by the oriented binding of anti-AFB1 antibodies onto the ProA domain and AFB1 in series. Consequently, a low detection limit (10 ng/mL) has been achieved for mycotoxin SPR immunosensor by using GBP-ProA fusion proteins as a

A Quarz Crystal Microbalance (QCM) consists of a thin quartz disk with a electrodes plated. The application of an external electrical potential to a piezoelectric material produces internal mechanical stress. As the QCM is piezoelectric, an oscillating electric field applied across the device induces an acoustic wave that propagates through the crystal and meets minimum impedance when the thickness of the device is a multiple of a half wavelength of the acoustic wave. Deposition of a thin film on the crystal surface decreases the frequency in

As described, the mycotoxins, such are Aflatoxins are toxical fungal metabolites that can occur in primary food products. In order to new biosensor development we focused our attention also on Ochratoxin A (OTA), which was discovered as a metabolite of *Aspergillus Ochraceus (*Van der Merwe et al*.*, 1965). This mycotoxin generally appears during storage of cereals, coffee, cocoa, dried fruit, pork etc. and occasionally in the field of grapes. It may also be present in blood and kidneys of animals that have been fed on contaminated feeds. Animal studies indicated that this toxin is carcinogenic (Turner et al., 2009). Therefore, the European Commission has fixed maximum concentration of OTA in foodstuffs: 3 g/kg (7.4 nM) for cereal products and 5 g/kg (12.4 nM) for roasted coffee, respectively (Commission

The establishment of efficient method of this analyte detection is therefore of high importance. In addition to traditional, but expensive and time-consuming methods such as liquid chromatography, new trends consist in development portable and easy to use

Most of the biosensors for this analyte detection developed so far were based on electrochemical detections such as oxidation of OTA at glassy carbon electrode (limit of

to use this assay for detection of AFB1 in maize within the regulatory limits.

Aflatoxin B1 developed using fusion proteins as a linker.

fusing gold binding polypeptides (GBP) to protein A (ProA).

**5. QMC biosensor for others mycotoxins** 

Regulation No. 1881/2006, 19 December 2006).

biosensors (Siontorou et al. ,1998).

as a blank matrix.

crosslinker. ( Ko et al*.,* 2010).

a portion to the mass of the *film*.

Optical sensors based on excitation of surface plasmons, commonly referred to as surface plasmon resonance (SPR) sensors, belong to the group of refractometric sensing devices. Development of SPR sensors for detection of chemical and biological species has gained considerable momentum, and the number of publications reporting applications of SPR biosensors for detection of analytes related to medical diagnostics, environmental monitoring, and food safety and security has been rapidly growing.

SPR affinity biosensors are sensing devices which consist of a biorecognition element that recognizes and is able to interact with a selected analyte and an SPR transducer, which translates the binding event into an output signal. The biorecognition elements are immobilized in the proximity of the surface of a metal film supporting a surface plasmon.

Analyte molecules in a liquid sample in contact with the SPR sensor bind to the biorecognition elements, producing an increase in the refractive index at the sensor surface, which is optically measured.

The change in the refractive index produced by the capture of biomolecules depends on the concentration of analyte molecules at the sensor surface and the properties of the molecules. If the binding occurs within a thin layer at the sensor surface of thickness, the sensor response is proportional to the binding-induced refractive index change. (Homola, 2008). The SPR principle is reported in Fig.4.

These biosensors show several advantages such as small sample volumes (µL volumes) and reusable metal chips.

Fig. 4. SPR biosensor principle, surface plasmons are excited by polarised laser beam at certain angle and the intensity of reflected light is measured.

Authors published data obtained using a SPR biosensor for Aflatoxin detection in maize extracts (Cuccioloni et al.).

In this paper different dilutions of Aflatoxin-containing and Aflatoxin-free fractions were added to the elastase-functionalized surface, and each response kinetic was routinely followed and analyzed as described above. The regeneration of the elastase monolayer was carried out as previously described. Detection procedures were replicated on different days on both the same and different elastase-functionalized surfaces. Additionally, the assessment of the number of regeneration cycles that a sensor surface can withstand without a significant loss of the sensitivity and accuracy of the assay and the stability of the sensing surface throughout multiple measurements were evaluated.

*Limits of Detection and Quantitation:* In compliance with the IUPAC rules, the limit of detection (LOD) was calculated as three times the standard deviation of the blank measurements. The limit of quantification (LOQ) is calculated as 10 times the standard

Optical sensors based on excitation of surface plasmons, commonly referred to as surface plasmon resonance (SPR) sensors, belong to the group of refractometric sensing devices. Development of SPR sensors for detection of chemical and biological species has gained considerable momentum, and the number of publications reporting applications of SPR biosensors for detection of analytes related to medical diagnostics, environmental

SPR affinity biosensors are sensing devices which consist of a biorecognition element that recognizes and is able to interact with a selected analyte and an SPR transducer, which translates the binding event into an output signal. The biorecognition elements are immobilized in the proximity of the surface of a metal film supporting a surface plasmon. Analyte molecules in a liquid sample in contact with the SPR sensor bind to the biorecognition elements, producing an increase in the refractive index at the sensor surface,

The change in the refractive index produced by the capture of biomolecules depends on the concentration of analyte molecules at the sensor surface and the properties of the molecules. If the binding occurs within a thin layer at the sensor surface of thickness, the sensor response is proportional to the binding-induced refractive index change. (Homola, 2008).

These biosensors show several advantages such as small sample volumes (µL volumes) and

Fig. 4. SPR biosensor principle, surface plasmons are excited by polarised laser beam at

Authors published data obtained using a SPR biosensor for Aflatoxin detection in maize

In this paper different dilutions of Aflatoxin-containing and Aflatoxin-free fractions were added to the elastase-functionalized surface, and each response kinetic was routinely followed and analyzed as described above. The regeneration of the elastase monolayer was carried out as previously described. Detection procedures were replicated on different days on both the same and different elastase-functionalized surfaces. Additionally, the assessment of the number of regeneration cycles that a sensor surface can withstand without a significant loss of the sensitivity and accuracy of the assay and the stability of the sensing

*Limits of Detection and Quantitation:* In compliance with the IUPAC rules, the limit of detection (LOD) was calculated as three times the standard deviation of the blank measurements. The limit of quantification (LOQ) is calculated as 10 times the standard

certain angle and the intensity of reflected light is measured.

surface throughout multiple measurements were evaluated.

monitoring, and food safety and security has been rapidly growing.

which is optically measured.

reusable metal chips.

extracts (Cuccioloni et al.).

The SPR principle is reported in Fig.4.

deviation of the blank measurements. Aflatoxin-free certified T400A maize sample was used as a blank matrix.

Calibration Curve: Biosensor-based assay was applied for the determination of AFB1 using spiked maize samples (Figure 3). The analysis of the binding of AFB1 to elastase over the concentration range 1−50 μg/kg reported that the response for the optimized assay was linear in the range between 1.67 and 17.8 μg/kg. The calibration procedure was replicated on three different days. The experimentally measured lower limit of the linear range was 1.67 μg/kg of AFB1, whereas the KD was 0.91 μM (≈250 μg/kg) AFB1. The detection limits reached allow us to use this assay for detection of AFB1 in maize within the regulatory limits.

Recently some authors presented during a Nanotechology Conference a SPR biosensor for Aflatoxin B1 developed using fusion proteins as a linker.

Because one of the main goal in the development of SPR immunosensors is efficient immobilization of antibodies. Conventional methods, such as self-assembled monolayers (SAMs) of alkanethiols cause antibodies to be random oriented. To improve antibody linker and orientation in their work, the authors constructed a novel fusion protein by genetically fusing gold binding polypeptides (GBP) to protein A (ProA).

The resulting GBP-ProA protein was directly self-immobilized onto SPR gold chip surfaces via the GBP portion, followed by the oriented binding of anti-AFB1 antibodies onto the ProA domain and AFB1 in series. Consequently, a low detection limit (10 ng/mL) has been achieved for mycotoxin SPR immunosensor by using GBP-ProA fusion proteins as a crosslinker. ( Ko et al*.,* 2010).

#### **5. QMC biosensor for others mycotoxins**

A Quarz Crystal Microbalance (QCM) consists of a thin quartz disk with a electrodes plated. The application of an external electrical potential to a piezoelectric material produces internal mechanical stress. As the QCM is piezoelectric, an oscillating electric field applied across the device induces an acoustic wave that propagates through the crystal and meets minimum impedance when the thickness of the device is a multiple of a half wavelength of the acoustic wave. Deposition of a thin film on the crystal surface decreases the frequency in a portion to the mass of the *film*.

As described, the mycotoxins, such are Aflatoxins are toxical fungal metabolites that can occur in primary food products. In order to new biosensor development we focused our attention also on Ochratoxin A (OTA), which was discovered as a metabolite of *Aspergillus Ochraceus (*Van der Merwe et al*.*, 1965). This mycotoxin generally appears during storage of cereals, coffee, cocoa, dried fruit, pork etc. and occasionally in the field of grapes. It may also be present in blood and kidneys of animals that have been fed on contaminated feeds. Animal studies indicated that this toxin is carcinogenic (Turner et al., 2009). Therefore, the European Commission has fixed maximum concentration of OTA in foodstuffs: 3 g/kg (7.4 nM) for cereal products and 5 g/kg (12.4 nM) for roasted coffee, respectively (Commission Regulation No. 1881/2006, 19 December 2006).

The establishment of efficient method of this analyte detection is therefore of high importance. In addition to traditional, but expensive and time-consuming methods such as liquid chromatography, new trends consist in development portable and easy to use biosensors (Siontorou et al. ,1998).

Most of the biosensors for this analyte detection developed so far were based on electrochemical detections such as oxidation of OTA at glassy carbon electrode (limit of

Biosensors for Aflatoxins Detection 155

important for binding OTA to DNA aptamer. In our opinion the described biosensor would

Microarrays provide a powerful analytical tool for the simultaneous detection of multiple

Research on microarrays as multianalyte biosystems has generated increased interest in the last decade. The main feature of the microarray technology is the ability to simultaneously detect multiple analytes in one sample by an affinity-binding event at a surface interface. In some cases immunoanalytical microarrays have the potential to replace conventional chromatographic techniques. They are applied if the number of samples is high or analysis by current methods is difficult and/or expensive. Therefore, microarray platforms have a great potential as monitoring systems for the rapid assessment of water or food samples. Antibody-based microarrays are a powerful tool for analytical purposes, also for Aflatoxins detection application. Immunoanalytical microarrays are a quantitative analytical technique using antibodies as highly specific biological recognition elements. They can be designed for a variety of analytical applications producing rapid results with low limits of detection

For these reasons in association to some biosensors for Aflatoxins examples, we reported in this Chapter also a feasibility study, made in our laboratories, on application of antibodies microarrays for simultaneous analysis of two different mycotoxins (Aflatoxin-B1 and Fumonisin B1). In this work we developed a competitive immunoassay in a microarray format and with the described method observed different microarray patterns in samples containing Aflatoxin-B1 or Fumonisine or either analytes at a ppb concentration range (Lamberti et al., 2009). The quality of the microarray data is comparable to data generated by a microplate-based immunoassay (ELISA), but further investigations are needed in order to better characterize these methods when applied for food contaminants determination. In any case we hope that our results can confirm the feasibility to develop hapten microarrays as for the immunochemical analysis of mycotoxins, as above described for others small organic molecules (e.g. bacterial toxins or

Enzyme linked immunosorbent assay (ELISA) and fluorescence immunoassay (FIA) are excellent survey tools for many analitycal purpose because of their high-throughput, user friendliness, and field portability. These important characteristics make immunoassays attractive tools for food testing by regulatory agencies to ensure food safety. Immunoassay is traditionally performed as individual test, however in many cases it is necessary to perform a panel of tests on each sample (detection of drug residues). To address this requirement, microarray-based immunoassay technologies have been developing utilizing microarray platform (multianalyte analysis) and classic immunoassay (multi-samples

In recent years, the antibody microarray technology has made significant progress, going from proof -of-concept designs to established high-performing technology platforms capable of targeting non-fractionated complex samples, as proteoma (Blohm & Guiseppi-

Microarrays consist of immobilized biomolecules spatially addressed on planar surfaces, microchannels or microwells, or an array of beads immobilized with different biomolecules.

analytes in a single experiment and consist of a biosensor *micro* o *nano* arrays.

be applied also for Aflatoxins detection.

(LOD).

analysis).

Elie., 2001).

biological warfare agents).

**6. Microarray for aflatoxin B1 detection** 

detection (LOD) 0.26 M) (Oliveira et al., 2007) or reduction of horseradish peroxidase (LOD 0.25 nM) (Alonso-Lomillo et al., 2010 ).

Immunosensor based on quartz crystal microbalance (QCM) was recently reported as well (Tsai *et al.,*2007). In this sensor anti-OTA antibodies were immobilised on a surface of 16 mercaptohexadecanoic acid. The detection based on the competitive binding between free OTA and that conjugated with BSA provided LOD 40 nM.

Recently a DNA aptamer sensitive to OTA has been developed (Cruz-Aguado et al., 2008). This aptamer was able to recognize OTA with sensitivity in a ppb level and with high selectivity. The electrochemiluminiscence biosensor using aptamers as receptors was recently developed (LOD 17 pM).

Thus most of the biosensors for mycotoxin OTA reported were based on indirect detection methods. Would be, however, rather useful to develop biosensor based on direct method that do not require additional modification of receptor or complicated multi stage assay. In a recent work Prof.T.Hianik (Comenius University, Bratislava, Slovakia) made therefore attempt to develop biosensor for OTA based on thickness shear mode acoustic method (TSM) using biotinylated DNA aptamers immobilised on a surface of quartz crystal transducer covered by neutravidin (Lamberti et al. 2011) .

TSM is certain analogy of QCM, however, in addition to mass, the TSM determines also the viscosity contribution arising from the friction between biolayer and the surrounding buffer (Fig.5).

Fig. 5. Propagation of acoustic wave from the sensor surface

This is important for detection of small molecules, such are mycotoxins for which the QCM detection is difficult due to small molecular weight of the analyte. We showed that TSM allowing detecting this mycotoxin with LOD 30 nM and with good selectivity. He also studied the stability of DNA aptamers depending on concentration of calcium ions, that are

detection (LOD) 0.26 M) (Oliveira et al., 2007) or reduction of horseradish peroxidase (LOD

Immunosensor based on quartz crystal microbalance (QCM) was recently reported as well (Tsai *et al.,*2007). In this sensor anti-OTA antibodies were immobilised on a surface of 16 mercaptohexadecanoic acid. The detection based on the competitive binding between free

Recently a DNA aptamer sensitive to OTA has been developed (Cruz-Aguado et al., 2008). This aptamer was able to recognize OTA with sensitivity in a ppb level and with high selectivity. The electrochemiluminiscence biosensor using aptamers as receptors was

Thus most of the biosensors for mycotoxin OTA reported were based on indirect detection methods. Would be, however, rather useful to develop biosensor based on direct method that do not require additional modification of receptor or complicated multi stage assay. In a recent work Prof.T.Hianik (Comenius University, Bratislava, Slovakia) made therefore attempt to develop biosensor for OTA based on thickness shear mode acoustic method (TSM) using biotinylated DNA aptamers immobilised on a surface of quartz crystal

TSM is certain analogy of QCM, however, in addition to mass, the TSM determines also the viscosity contribution arising from the friction between biolayer and the surrounding buffer

This is important for detection of small molecules, such are mycotoxins for which the QCM detection is difficult due to small molecular weight of the analyte. We showed that TSM allowing detecting this mycotoxin with LOD 30 nM and with good selectivity. He also studied the stability of DNA aptamers depending on concentration of calcium ions, that are

0.25 nM) (Alonso-Lomillo et al., 2010 ).

recently developed (LOD 17 pM).

(Fig.5).

OTA and that conjugated with BSA provided LOD 40 nM.

transducer covered by neutravidin (Lamberti et al. 2011) .

Fig. 5. Propagation of acoustic wave from the sensor surface

important for binding OTA to DNA aptamer. In our opinion the described biosensor would be applied also for Aflatoxins detection.
